Monochromatic fluid treatment systems

ABSTRACT

Methods, systems and apparatus for photo-processing of fluids, particularly complex fluids, such as blood products, pharmaceuticals, injectables and vaccines, are provided. The disclosed methods and systems employ non-laser light source(s) to generate monochromatic light energy, preferably in the range of 260 nm to 310 nm, for fluid treatment. Advantageous processing regimens and/or adjunct additives and/or agents may also be used to achieve desired and/or enhanced results, e.g., inactivation of pathogens, bacteria and/or viruses, modulation of immune response, and/or leukoreduction. Particularly preferred embodiments include specific wavelengths, novel temperature control systems and geometric/structural arrangements that provide enhanced processing results and/or efficiencies. The disclosed methods, systems and apparatus achieve desirable results in a broad range of diagnostic, therapeutic and treatment applications, and generally provide enhanced operating efficiencies and/or processing results in application modalities that employ a broad range of photo-activated and/or photo-responsive materials and/or compounds.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation-in-part and division of aco-pending, commonly assigned U.S. patent application entitled“Monochromatic Fluid Treatment Systems,” which was assigned Ser. No.09/805,610 and was filed on Mar. 13, 2001, the entire contents of whichare incorporated herein by reference.

BACKGROUND

1. Technical Field

The present disclosure relates to systems for photo-processing offluids, and more particularly to systems for photo-processing of complexfluids, such as blood products, pharmaceuticals, injectable solutions,and vaccines using non-laser light source(s) to generate and delivermonochromatic light at advantageous wavelength(s) in advantageoussystems to affect desirable results.

2. Background of Related Art

Efforts have been devoted to treatment regimens for complex fluids,e.g., fluids having medical and/or health-related uses and applications,such as vaccines, pharmaceuticals, injectable solutions, blood productsand the like. These efforts have focused in part on technologies andtreatment systems to remove, inhibit and/or destroy unwanted fluidcomponents. Treatment regimens aimed at alternative objectives, such asleukoreduction (i.e., the removal of white blood cells to avoidpotentially undesirable effects), have also received attention.

Significant research and development attention has focused on fluids andmaterials that are collected for transfusion and/or transplantation,e.g., blood products and blood components. (“Pathogen Inactivation inLabile Blood Products” in Transfusion Medicine, Vol. 11, pp 149–175,2001) In assuring the safety of such materials, significant reliance isplaced on pre-transfusion donor evaluation and testing. Despite currentefforts, transfusions and transplantations are nonetheless implicated inthe transmission of viral, bacterial and protozoan diseases. Newinfectious agents continue to be identified in the donor population,giving rise to increased challenges and concerns among those responsiblefor ensuring a safe and reliable supply of neededtransfusion/transplantation materials. Testing for unknown pathogens(e.g., HIV in the late 1970's) remains problematic. Moreover,limitations necessarily exist with respect to the effectiveness of donorscreening efforts, e.g., donation volumes, screening/testingimpediments, logistical issues, etc. Reliable screening and/ordecontamination regimens are of even greater importance for individualsreceiving multiple cycles of chemotherapy and/or hematopoietictransplantation because of the cumulative risk associated with repeatedtransfusion/transplantation episodes.

Current research activities and perspectives in the treatment ofplatelets are discussed in a recently published article. (L. Corash,“Inactivation of Viruses, Bacteria, Protozoa, and Leukocytes in PlateletConcentrates: Current Research Perspectives,” Transfusion MedicineReviews, Vol. 13, No. 1, January, 1999). As noted in the article, riskassociated with transfusion-associated infections could be reducedthrough development and implementation of decontamination processes thatare effective against a broad array of infectious pathogens, regardlessof type, including infectious agents not detected through currentdiagnostic tests. Decontamination processes are preferably effectiveagainst cell-free, cell-associated and latent pathogen forms. The needfor this breadth in decontamination capability is exemplified by humanimmunodeficiency virus (HIV), which is cell-free in plasma,cell-associated in leukocytes, and in latent pro-viral form integratedinto genomic leukocyte nucleic acid. Moreover, decontamination processesneed to be active against a broad spectrum of bacteria, includingintracellular bacterial forms, to avoid possible bacterial regrowthduring storage.

Several potential inactivation technologies for treatment of plateletconcentrates have been investigated/described, including psoralensactivated with long-wavelength ultraviolet light, merocyanine 540activated with visible light, riboflavin and methylene blue, andphthalocyanines activated with red light. Of these treatmenttechnologies, attention has focused on the chemistry and associatedbonding properties of different compounds, with psoralens receiving thegreatest level of attention to date.

Psoralens are planar furocoumarins, many of which are synthesized byplants and ingested as foods. Psoralens preferentially bind to nucleicacid, both RNA and DNA, and vary widely with respect to solubility,nucleic acid affinity, and side reactions, e.g., active oxygen speciesgeneration. Investigations have shown that psoralen photochemicaltreatments can be effective for inactivation of bacteria, RNA virusesand DNA viruses. Exemplary psoralen compounds are described in U.S. Pat.No. 5,654,443 to Wollowitz et al.; U.S. Pat. No. 5,709,991 to Lin etal.; and U.S. Pat. No. 6,171,777 B1 to Cook et al.

Cerus Corporation (Concord, Calif.) has developed a series of psoralencomponds that are being evaluated for their ability to inactivatepathogens in blood products. In one psoralen-based process underdevelopment by Cerus, a platelet suspension, which may be pooled fromindividual units from several donors, is transferred to a steriledisposable bag containing Cerus' S-59 psoralen compound. Theblood-containing bag is illuminated with ultraviolet light forapproximately three minutes. The Cerus procedure is intended to preventthe pathogen from reproducing and infecting a transfusion recipient.Cerus envisions the treated platelet suspension being ready fortransfusion to a recipient.

The amount of psoralen required for efficient removal varies with thetarget species. Therefore, the inactivation levels achieved usingphotochemical treatment of blood products are a function of both UV doseand the concentration of the added chemical agent. The S-59 process, forexample has a very strong dependence on the concentration of theirproprietary psoralen, S-59. Pathogen inactivation requires 1000 timesthe amount of S-59 that leukocyte inactivation does. The range of UVdoses required to accomplish the same task is smaller. Why? It may bethat during the the experiments using S-59 it was not possible to adjustUV dose. More likely, the process is limited by the delivery of thechemical to the nucleic acid, not the activation of the chemical. Fromrecent literature it appears that the efficacy of S-59 is limited by thekinetics of S-59 “uptake”. In biological material that readily absorbsS-59 the DNA is accessible and a lower doses of additive can be used. Itis believed that this same process will limit all photochemicaltreatments including Inactine. Recent literature (see D. C. Hooper,Emerging Infectious Diseases (7)2, 2001) has found that certain speciesthat are resistant to psoralen-like compounds have this resistancebecause they are able to modify their permeability to the toxin. Thistheory is also supported by lab findings using S-59 that show speciesspecific log removal rates. Some of the species that are most resistantare the same ones identified in the Hooper reference. A similar issue isthe accepted inability of S-59 to inactivate preformed spores. Thesespores are inactivated by UV. Therefore, a combination of directactivation by UV and by photochemical may be beneficial. This is similarto issues associated with cryptosporidium and chlorine in drinkingwater—crypto oocysts are not inactivated by chlorine, resulting inseveral outbreaks of cryptosporidiosis. Cryptosporidian is inactivatedby UV.

This effect is also seen in systems using riboflavin as thephotosensitizer (Goodrich et al., U.S. Pat. No. 6,277,337) developed byGAMBRO BCT. However, in this work inactivation is not only a function ofthe target pathogen, but also on dose and wavelength of the appliedlight. (It is possible that the wavelength of the light source will alsoeffect the efficacy of psoralen based processes and that this effect hasnot been documented due to limitations in available light sources.) Theriboflavin data presented in U.S. Pat. No. 6,277,337 shows that for someorganisms, specifically double-stranded viruses, a combination ofvisible and UV light was needed. No explanations for this requirementswere made. It is possible that the inactivation of the full range ofpathogens may require more than one process.

Additionally, treatment modalities based on photochemical additivesrequire, by definition, that an external agent/material be added to thefluid being treated, with the inherent issues and uncertaintiesassociated therewith. Moreover, beyond the requirement that externalagent(s)/material(s) be added to the fluid system to effect treatment,other limitations and/or requirements have been identified with respectto certain psoralen-based treatment modalities. For example, longtreatment times (up to 4 hours of UVA illumination with8-methoxypsoralen) and reduced ambient oxygen levels associated withcertain psoralen-based systems are not compatible with requirements forease of operation, e.g., in clinical blood bank environments. Inaddition, the addition of a free radical quencher, e.g., rutin (anaturally occurring flavenoid), may be required to prevent plateletdamage due to active oxygen species, i.e., to preserve in vitro plateletfunction. The addition of free radical quencher(s) like rutin furtherincreases the complexity of treatment systems.

As discussed by Corash, high UVA doses have also been required forcertain psoralen compounds, e.g., from 24 to 70 J/cm² for4′-(amino-methyl)-4,5′,8-trimethlypsoralen (AMT), to treat plateletsuspensions in 100% plasma. AMT has also exhibited questionabletoxicology profiles. Reductions in plasma protein concentration, e.g.,to 15% through use of synthetic platelet additive solution, is effectivein reducing energy requirements, e.g., viral inactivation with AMT at2.4 J/cm², but is not practical for large-scale operations. (TransfusionMedicine Reviews, Vol. 13, No. 1, pp. 21, 23.)

Margolis-Nunno et al. evaluated the treatment of HIV-infected plateletconcentrates with an AMT/rutin system using two types of ultravioletradiation, UVA and UVA1. UVA was characterized as broad-band ultravioletA light, having a wavelength of between 320 and 400 nm, and UVA1 wascharacterized as narrow-band UVA light, having a wavelength between 360and 370 nm. Margolis-Nunno et al. concluded that wavelength was animportant consideration in these treatment systems and that, at similarfluences, the tested UVA was more injurious to platelets than was UVA1.(Margolis-Nummo et al., “Psoralen-Mediated Photodecontamination ofPlatelet Concentrates: Inactivation of Cell-free and Cell-associatedForms of Human Immunodeficiency Virus and Assessment of PlateletFunction In Vivo,” Transfusion, Vol. 37, September 1997, pp. 889–895.)

Photodynamic therapy (PDT) has also received significant research anddevelopment attention, particularly for cancer indications. In typicalPDT treatment regimens, a photosensitizer is administered systemically,e.g., a porphyrin derivative, and after a period in which thephotosensitizer accumulates within a target tissue, a measured amount oflight is applied to the target region. Beyond cancer treatment, PDTtreatments have been developed for use against ophthalmologicalconditions, cardiovascular conditions (e.g., artherosclerosis andrestenosis), and immune-mediated conditions (e.g., psoriasis).

El-Ghorr and Norval describe the biological effects of narrow-band UVBirradiation, e.g., in treating psoriasis, as compared to conventionalbroadband UVB irradiation effects. (El-Ghorr et al., “Biological Effectsof Narrow-Band (311 nm TL01) UVB Irradiation: A Review,” Journal ofPhotochemistry and Photobiology B: Biology 38 (1997), 99–106.) The TL01lamp tested by El-Ghorr and Norval emits a narrow peak (51% of theradiant energy at 311 nm). Based on limited available test data, theTL01 lamp appears to be more suppressive than broad-band UVB duringphototherapy with respect to natural killer cell activity and thefunction of mononuclear cells, as measured by lymphoproliferation andcytokine production. El-Ghorr and Norval suggest that the noted effectof the TL01 lamp may be both dose related and wavelength dependent.

In a further study, Prodouz et al. evaluated the use of laser-UV intreating blood products to inactivate poliovirus. (Prodouz et al., “Useof Laser-UV for Inactivation of Virus in Blood Products,” Blood, Vol.70, No. 2, August, 1987, pp. 589–592.) The Prodouz et al. studyuniformly irradiated samples with a XeCl excimer laser that delivered 40nsec pulses of UV at 308 nm. This work noticed that at higher powers,including the very high peak power delivered from the pulsed laser,there was a greater reduction in platelet function. Even still, Prodouzet al. concluded that, when using a pulsed excimer laser at 308 nm,there exists a window of efficacy for exposure doses between 10.8 and21.5 J/cm² and peak intensities of less than 0.17 MW/cm² within which ahardy virus is significantly inactivated and platelet and plasmaproteins are minimally affected. This work inactivate polio virus. Theefficacy of 308 nm on more complex targets has not been determined.

Andreu et al. evaluated ultraviolet irradiation of platelet concentratesto reduce HLA immunization by placing suspended platelet concentratesbetween quartz plates and irradiating with UV-B rays at 310 nm. Andreuet al. concluded that in vitro function of platelet concentrates remainsunaffected by UV-B up to 2.25 J/cm², but that higher energies inhibitthe aggregation induced by ADP and collagen. Andreu et al. identified agap in treatment effects with UV-B rays between 0.2 J/cm², where thedesired inhibitory effect on immunologic recognition is probablycomplete, and above 2 J/cm², where detrimental effect on plateletfunction appears. (Andreu et al., “Ultraviolet Irradiation of PlateletConcentrates: Feasibility in Transfusion Practice,” Transfusion, Vol.30, No. 5—1990, pp. 401–406.)

U.S. Pat. Nos. 4,726,949; 4,866,282; and 4,952,812 to Miripol et al.disclose blood product irradiation methods and systems for inactivatingwhite blood cells. The Miripol et al. treatment regimens employultraviolet radiation predominantly of a wavelength of 280 to 320 nm, anintensity of 4 to 20 mW/cm², and a total energy exposure of 800 to20,000 mJ/cm². Eight to twelve conventional, high intensity bulbs aredescribed for use in irradiating blood contained within a flexible,collapsible poly(ethylene-vinyl) acetate plastic bag, the plastic bagtypically being stretched on a framework. An exhaust fan is provided inthe back of the Miripol et al. apparatus to exhaust heat generated bythe high intensity bulbs. It is interesting to note that while in thiswork it was claimed that the process was novel because it operated at adifferent surface dose (J/cm2), a closer read of the data shows that theapplied surface dose required for a successful treatment increases withthe thickness of the blood product. The critical parameter is thereforenot the applied surface dose, but how that dose is distributed withinthe fluid volume.

Despite efforts to date, there exists a continuing need for systems thatfacilitate treatment of complex fluids, e.g., blood products,pharmaceuticals, injectable solutions and vaccines. In particular,systems applicable to high value/complex fluids that effectively andreliably achieve desirable levels of pathogen inactivation, modulationof immune response, medical therapy and/or chemical synthesis, withoutnegatively impacting desirable characteristics of the high value/complexfluid, are needed. While significant attention has been devoted todeveloping and evaluating a variety of photosensitive agents in treatingpathogens and the like, the potential effects and/or influences of lightsource(s) and/or wavelength characteristics of light on complex fluidtreatment systems have received less intensive study. While UV-Birradiation is considered an option for leukocyte inactivation pathogenusing only UV light is not considered a viable process. Indeed, Cook etal. state that treatment of blood products to eliminate transmission ofdiseases by inactivating pathogens through UV alone is “completelyincompatible with maintenance of red cell function.” (U.S. Pat. No.6,171,777 B1, col. 2, lines 58–64.) A more recent review of “PathogenInactivation of Labile Blood Products (Transfusion Medicine, Vol. 11,149–175, 2001), did not consider chemical free processing of pathogensusing UV light.

SUMMARY OF THE DISCLOSURE

The present disclosure provides innovative systems for photo-processingof fluids, particularly high value and/or complex fluids, such as bloodproducts, pharmaceuticals, injectable solutions and vaccines. Thedisclosed systems employ advantageous light source(s) and processingregimens, whether alone or in combination with adjunct additives and/orphotoactive agents, to achieve desired results. Preferred systemsaccording to the present disclosure are effective in inactivatingpathogens, bacteria and/or viruses, modulation of immune response,and/or leukoreduction, without negatively impacting desirable componentsand/or attributes of the treated fluid, and achieve desirable results ina broad range of diagnostic, therapeutic and treatment applications.Preferred systems further provide enhanced operating efficiencies and/orprocessing results in application modalities that employ a broad rangeof photo-activated and/or photo-responsive materials and/or compounds.

One advantageous aspect of the disclosed systems relates to an abilityto utilize light energy to limit and/or minimize degradation of certainfluid properties and/or components, e.g., potential degradation throughheat, energy activation or the like, while simultaneously maximizing thedesired effect(s) through use of such light energy. The desired effectsmay be biologic, e.g., pathogen inactivation, or chemical, e.g.,excitation of specific psoralen-based adducts, or a combination thereof.The generation of harmful and/or toxic byproducts is also advantageouslyminimized or avoided according to the present disclosure.

As described earlier there are limitations in the range of pathogensinactivated by either photosensitized reactions (particularly usingpsoralen or riboflavin) or light. The ability to initiate bothphotosensitized inactivation, and direct UV disinfection with a singlesource is therefore appealing. This work proposes such a system. In thisprocess UV light in the range of 282 of 320 nm is applied, 290 and 308nm are specifically highlighted. This light activates photosensitizedreactions of larger genome pathogens best treated photochemically, aswell as smaller single stranded targets best inactivated by light alone.

According to the present disclosure, light source(s) are provided thatsupply light energy having highly advantageous effect(s) on treatedfluids, particularly high value and/or complex fluids such as bloodproducts, pharmaceuticals, injectable solutions and vaccines. Thepresent disclosure further provides system design and processingregimens that, when used in conjunction with disclosed light source(s),provide advantageous fluid processing results, both in batch andcontinuous flow treatment systems.

The present disclosure is also directed to a method for treating acomplex fluid which includes introducing a supply of complex fluid intoa treatment zone, the complex fluid including a nucleic acid; adding aphotoactive compound to the complex fluid; and applying light energy tothe complex fluid and the photoactive compound in said treatment zone.The light energy is supplied from a light source that generates lightenergy having a designated wavelength below 340 nm. The light energyfrom the light source is effective to substantially excite said nucleicacid of the complex fluid and to substantially excite said photoactivecompound.

Preferably, the complex fluid is a blood-based product and furtherincludes biological proteins which are inactivated by ultraviolet light.Additionally, it is presently envisioned that the light source is anon-laser light source and said light energy from the non-laser lightsource is substantially monochromatic. Alternatively, the light sourceis configured to produce polychromatic output. In a preferredembodiment, the light source selectively adjusts a gas mixturecontaining a rare gas or halogen so as to produce the polychromaticoutput.

It is envisioned that the photoactive compound used in the disclosedmethod can be riboflavin. Additionally, the nucleic acid excited by thelight energy from the light source is single stranded and belongs to apathogen and the photoactive compound is effective at inactivatingpathogens with double stranded nucleic acid.

BRIEF DESCRIPTION OF FIGURE(S)

To assist those of skill in the art to which the subject matter of thepresent disclosure appertains, reference is made to the accompanyingdrawings and associated detailed description, in which:

FIG. 1 is a perspective view of one aspect of a treatment apparatusaccording to an embodiment of the present disclosure;

FIG. 2 is a cross sectional view of a first aspect of the treatmentapparatus of FIG. 1, taken along line 2—2;

FIG. 3 is a schematic cross sectional view of a second aspect of atreatment apparatus according to an embodiment of the presentdisclosure;

FIG. 4 is a schematic cross sectional view of combined first and secondaspects of a treatment apparatus according to an embodiment of thepresent disclosure;

FIG. 5 is a schematic perspective view of a treatment apparatusaccording to an alternative embodiment of the present disclosure;

FIG. 6 is a schematic cross sectional view of the treatment apparatus ofFIG. 5, taken along line 6—6;

FIG. 7 is a schematic cross sectional view of a treatment apparatusaccording to a further alternative embodiment of the present disclosure;

FIG. 8 is a schematic cross sectional view of a treatment apparatusaccording to an additional alternative embodiment of the presentdisclosure;

FIG. 9 is a graphical representation which illustrates the e-coli doseresponse based on experimental results obtained according to anembodiment of the present disclosure;

FIGS. 10 a and 10 b demonstrate an algorithm for maximizing thethickness of fluids within the treatment systems described here;

FIG. 11 a is side elevational view of a reactor/lamp embodiment of thepresent disclosure which is well suited for flow through applications;

FIG. 11 b is a front elevational view of the lamp of FIG. 11 a;

FIGS. 12 a–12 b summarize the inactivation of PPV at 282 nm and 308 nmin samples of random donor platelets and fresh frozen plasma; and

FIG. 13 is a graphical representation which summarizes the amount of LDHreleased from platelets during processing at 282 and 308 nm. LDH is usedas a measure of cellular damage.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENT(S)

The present disclosure provides innovative systems for photo-processingof fluids, particularly high value and/or complex fluids, such as bloodproducts, pharmaceuticals, injectable solutions and vaccines. As usedherein, a “complex fluid” is a fluid that includes a plurality of fluidcomponents that are sensitive to and/or activated by light and/or heatenergy, wherein a first light-sensitive/light-activated/heat-sensitivefluid component is to be substantially preserved according to thedisclosed treatment regimen, and a secondlight-sensitive/light-activated fluid component is to be substantiallymodified, inactivated and/or eliminated according to the treatmentregimen. A “complex fluid” according to the present disclosure may alsoinclude added photoactive compound(s)/material(s), e.g., psoralen, andlight energy sensitivity/reactivity may be due in part to the presenceof such photoactive compound(s)/material(s).

The innovative systems of the present disclosure employ advantageouslight source(s) and processing regimens unique to the treatment ofcomplex fluids. The disclosed systems may be employed with or withoutphotoactive compounds and/or agents to achieve desired results, e.g.,inactivation of pathogens, bacteria and/or viruses, modulation of immuneresponse and/or leukoreduction. The disclosed systems achieve desirableresults in a broad range of diagnostic, therapeutic and treatmentapplications, and provide enhanced operating efficiencies and/orprocessing results in application modalities that employ a broad rangeof photo-activated and/or photo-responsive materials and/or compounds.

According to the present disclosure, light source(s) are provided thatsupply light energy having highly advantageous effect(s) on treatedfluids, particularly high value and/or complex fluids such as bloodproducts, pharmaceuticals, injectable solutions and vaccines. Thepresent disclosure further provides geometric, spectral, intensity andprocessing regimens that, when used in conjunction with disclosed lightsource(s), provide advantageous fluid processing results, both in batchand continuous/semi-continuous treatment systems.

Preferred light source(s) according to the present disclosure supplysubstantially monochromatic light at high average power outputs, butmoderate peak power outputs, thereby reducing or eliminating potentialdamage to high value/complex fluids due to undesirable heating and/ormulti-photon initiated processes. Thus, conventional laser light sourcesand conventional flash lamps are ineffective/less effective, and are tobe avoided according to the systems of the present disclosure. Pulsedlaser light sources are undesirable and ineffective according to thepresent disclosure at least in part due to the high peak power pulsesgenerated thereby. Conventional high intensity lamps, e.g., mercurylamps, fail to provide the wavelength flexibility, processingefficiency, intensity and carrier media preservation, that are criticalto treatment systems according to the present disclosure.

It has been found according to the present disclosure that use of thedisclosed high output, monochromatic light sources allows effectiveexploitation of advantageous treatment windows for high value and/orcomplex fluids, e.g., blood products, pharmaceuticals, injectablesolutions and vaccines. Moreover, use of high output, monochromaticlight sources as disclosed herein generate synergistic results incomplex fluid systems that utilize chemical and/or photoactive agents.

Before describing specific aspects of preferred treatment systemsaccording to the present disclosure, including attributes of preferredlight sources and associated apparatus/treatment regimens, a discussionof contemplated fluid treatment applications and/or techniques in whichthe disclosed treatment systems offer advantageous results is provided.This discussion of exemplary fluid treatment applications and/ortechniques is provided at a level of detail that will permit persons ofordinary skill in the art to effectively exploit the innovativetreatment systems disclosed herein to achieve advantageous results.Additional fluid treatment applications and/or techniques may also berecognized and/or devised for exploitation of the innovative treatmentsystems disclosed herein, as will be apparent to persons of ordinaryskill in the art from the detailed description that follows, and suchadditional fluid treatment applications and/or techniques are to bedeemed within the scope of the present disclosure.

In a first preferred embodiment of the present disclosure, a system isprovided for efficacious treatment of high value/complex fluids that maycontain undesirable pathogens, e.g., viral and/or bacterial components,through application of monochromatic light generated by a non-laserlight source at advantageous wavelength(s). Exemplary fluids fortreatment according to the disclosed treatment regimen include bloodproducts, pharmaceuticals, injectable solutions and vaccines. Accordingto this embodiment, high value/complex fluids are treated to inactivateundesirable pathogens without the addition of chemical additives,photochemical agents and the like, e.g., psoralens, thereby simplifyingthe treatment regimen and eliminating the need for quenchers and/orpost-treatment removal of added materials and/or byproducts.

The disclosed treatment system may be undertaken with respect to highvalue/complex fluids in real time, i.e., immediately upon the creationand/or availability of the target fluid for treatment. Thus, forexample, in the context of blood product or othertransfusable/injectable component treatment systems, the disclosedtreatment regimen may be advantageously employed immediately upon bloodproduct donation, immediately prior to blood product transfision, and/ora combination thereof. These processes can include a real time treatmentof the blood product as it is moving in the tubing. Alternatively,treatment systems may be deployed to treat high value/complex fluidsimmediately prior to aseptic packaging, e.g., in large-scale systems forsterilizing solutions prior to packaging thereof. Each of the foregoingtreatment systems may be batch, semi-batch, continuous orsemi-continuous in operation.

According to preferred embodiments of the disclosed system,substantially monochromatic light energy is delivered to the desiredhigh value/complex fluid to achieve maximal absorbance within or by thetarget pathogen(s), while simultaneously minimizing damage to thenon-pathogenic components and/or substrates, e.g., the carrier media, ofthe treated fluid. Thus, in the case of blood products, it has beenfound that particularly desirable pathogen inactivation results may beachieved, without deleterious effect to blood product components withinthe carrier media, by delivering substantially monochromatic light at awavelength of between 260 and 310 nm, and generally between 270 nm and308 nm. Preferred monochromatic wavelengths include 282 nm, 290 nm and308 nm, although additional wavelengths within the preferred rangesdisclosed herein are also deemed to be highly desirable. As used herein,substantially monochromatic light generally exhibits a wavelengthdistribution wherein the light energy falls predominantly within a rangeof +/−10 nm relative to the designated wavelength.

Pulsed laser light sources have also been found to affect anunacceptable level of damage to the carrier media. This disclosure notesthat the absorption characteristics of biological fluids have a rapid,and surprisingly sharp discontinuity near 300 nm. The change of a fewnanometers can have a significant effect. For example, recentmeasurements of platelets and plasma, demonstrated a change in opticaldensity of greater than 20 times between 270 and 310 nm. (Photochemistryand Photobiology, Vol. 71(5) 610–619, 2000) Clearly the processesinitiated by the absorption (or transmission) of light on thesebiological fluids will have a strong wavelength dependence and the term“UV-B” does not adequately define the light source. The light sourcesdisclosed here operating in, but not limited to, narrow bands centeredat 259, 282, 290 and 308 nm will each have distinct advantages.

In a further embodiment of the present disclosure, a treatment system isprovided in which high value/complex fluids may be treated to reliablyand efficaciously inactivate pathogen(s) contained therewithin, whereinthe treatment system includes one or more photoactivated compoundsand/or additives. Thus, according to the disclosed treatment system,conventional photoactivated compound(s) and/or additive(s) are combinedwith a treatment fluid, e.g., a blood product, pharmaceutical,injectable solution and/or vaccine, as is known in the art. However,unlike prior art treatment regimens, the disclosed system advantageouslyirradiates the combined fluid, i.e., high value/complex fluid andphotoactivated compound/additive combination, with substantiallymonochromatic light energy from a non-laser light source at preferredwavelength(s) and intensity(ies), and in preferred geometric/structuralarrangement(s), as described in greater detail hereinbelow.

According to the disclosed treatment regimen that includes aconventional photoactive compound/additive, e.g., one or more psoralens,dimethylmethylene blue, riboflavin and the like, pathogen inactivationmay be enhanced while minimizing unwanted side effects by irradiatingsuch fluid systems with substantially monochromatic light atwavelength(s) between 270 and 340 nm. Additionally it has been foundthat small differences in wavelength can have significant effects oncell function, pathogen inactivation, and excitation of photochemicaladditives. Particularly preferred wavelengths for photochemicaladditives include 308 nm, 320 nm and 351 nm. For pathogen inactivation,the optimal wavelengths will be 259, 282, 290 and 308 nm. Light deliveryto the treatment fluid is controlled such that the wavelength isadjusted and peak intensity levels minimized, thereby advantageouslyexciting the photoactive compound(s)/additive(s) to achieve the desiredresults. Thus, in psoralen-based embodiments of the present disclosure,sufficient light intensity is delivered within a narrow spectral rangeto excite specific adducts. According to such treatment regimens,desirable results are achieved, including inhibiting target pathogen(s)from reproducing/infecting a transfusion recipient, and/or generatingimproved immune response. Moreover, the systems of the presentdisclosure provide dose rates that speed these processes.

It is further contemplated according to the present disclosure thatparticularly advantageous results may be achieved byilluminating/irradiating a fluid system, e.g., a blood system thatincludes a photoactive compound/additive, so as to achieve the desiredactivation of the photoactive compound/additive and to additionallyeffect dissociation of the compound/additive. It is contemplated thatthe dual processing objectives may be achieved as part of theinactivation process, or in a subsequent monochromatic light-basedtreatment, e.g., in a continuous processing treatment system. Generationof an optimally effective adduct, e.g., an adduct that is wavelengthdependent, or generation of an optimal surface structure that iswavelength dependent facilitates successfully accomplishing both desiredresults according to the disclosed treatment system.

In another preferred embodiment of the present disclosure, monochromaticlight from a non-laser light source is advantageously utilized to effectleukoreduction to minimize or prevent blood platelet alloimmunization,i.e., the transfer of pathogenic immune response information throughblood transfusion. Thus, according to a preferred embodiment of thepresent disclosure, a blood system is treated with monochromatic lighthaving a wavelength at between 260 and 310 nm, generally between 270 and308 nm, and preferably at a wavelength of 282, 290 or 308 nm. Apreferred blood system is treated at an intensity of greater than 20mW/cm² to effect desired rates of leukoreduction. Substantiallymonochromatic light energy having the desired UV-B wavelength istypically generated from a non-laser light source, thereby moderatingenergy levels in the manner desired according to the disclosed treatmentregimen.

It is further contemplated according to the present disclosure thatmonochromatic light generated by a non-laser light source atpredetermined wavelengths will exhibit synergistic effects withdifferent adducts in photophoresis treatment regimens. Thus, it iscontemplated that monochromatic light may be used in connection withextracorporeal photophoresis, AIDs treatment, cancer treatment (e.g.,cutaneous T cell lymphoma (CTCL)), Lupus treatment, and other diseasetreatments and/or treatment regimens directed to conditions requiringmodulation of the immune system.

Additionally, it is contemplated that graft vs. host disease (GVHD) maybe treated through systems utilizing monochromatic light of apredetermined wavelength and intensity. GVHD treatment regimens may beachieved that optimally inactivate T-cells while preserving othersubstrates and components to enhance the likelihood of transplantsuccess. In particular, with stem cell transplants, photoactivation withan optimal light energy is believed to maximize inactivation ofT-lymphocytes and minimize damage to the hematopoietic stem cells. SeeAzuma et al. in Blood Vol. 96 (7) p. 2632 (2000).

Thus, for example, treatment regimens involving photoactive compoundsand/or agents having efficacy in treating the above-noted diseasesand/or conditions are believed to exhibit advantageous treatment resultswhen activated with monochromatic light, particularly monochromaticlight generated by a non-laser light source, producing “monochromatic”output at discreet wavelengths of between 250 and 400 nm, and preferably259 to 310 nm.

Additional treatment regimens utilizing substantially monochromaticlight are also contemplated according to the present disclosure,including body irradiation techniques and treatment of a variety ofmedical and health-related fluids. Thus, in a preferred embodiment ofthe present disclosure, monochromatic light delivery systems areprovided that accommodate irradiation of one or more portions of a body,e.g., a limb, extremity or the like. The light delivery system mayadvantageously permit introduction of the body portion to an enclosedchamber and/or entail paddle light sources that are easily and reliablypositioned adjacent the body region to be treated and/or provide faster,more comfortable systems for whole body irradiation. Upon irradiation ofthe target body region with monochromatic light of a desired wavelengthand intensity, photoactivation of the surface layer(s) thereof may beachieved with desirable result. It is noted that systems that producemonochromatic output by selecting a subset of the light sources outputusing filters, or covert the light sources output to another wavelengthusing phosphors, or isolate the infrared (heat) of the light sourcesfrom the target using fiber optics are limited in size or intensity.

It is additionally contemplated according to the present disclosure thatmonochromatic light of predetermined wavelength and intensity may beused to advantageously and reliably sterilize fluids, e.g., saline,interperitoneal fluid, vaccines, liquid pharmaceuticals, injectablefluids, and other sterilizable fluids. In particularly preferredembodiments, medical fluids are processed into a relatively thin filmand exposed to substantially monochromatic light generated by anon-laser light source at a wavelength between 260 nm and 310 nm toachieve advantageous, uniform dosing. Alternatively, thicker flowstreams may be processed, with engineered turbulence to achieve desireduniformity in dosing. Thus, improved sterilization results may beachieved for a range of fluids according to the treatment systemsdisclosed herein.

It is further contemplated according to the present disclosure thatmonochromatic light generated by a non-laser light source atpredetermined wavelength(s) and intensity(ies) may be utilized toactivate/promote chemical synthesis and/or chemical processing. Thus,the activation energy associated with a specific process step and/or thekinetic parameters associated with a particular chemical process may besupplied by such monochromatic light, thereby potentially boostingyields and speeding process rates. For example, processes that arebiologic in nature, e.g., activation/inactivation of biologic organismsinfluencing chemical processes, or chemical in nature, e.g., dependentupon the excitation of specific active site(s) and/or functionalgroup(s), may be promoted and/or enhanced through monochromatic lightenergy supplied according to the present disclosure.

In all cases, dose determination is not straightforward in opaquefluids. Previous disclosures have often mistaken surface dose with dosedelivered to the fluid volume. The large area sources disclosed hereinallow dose to be advantageously controlled through changes/modificationsin light source geometry. Typical systems require severe overdosing atsome volumes to ensure adequate dosing of others. The disclosedtreatment systems, however, provide a means to treat complex, opaquefluid volumes more uniformly. Additional analysis can identifywavelengths where absorption is minimized and scatter is maximized—thiswill produce a peaked intensity profile within the fluid. The thicknessof the fluid can therefore be engineered to enable more uniform dosing.In some cases, the use of light scattering, may achieve dosedistributions similar to two sided excitation, but with one sidedexcitation.

In short, substantially monochromatic light having predeterminedwavelength, geometry and intensity characteristics may be exploited toachieve and/or deliver significant benefits in a wide range ofapplications, systems and techniques according to the presentdisclosure. Through control of the wavelength, intensity and deliverycharacteristics of the monochromatic light, advantageous results areachieved in a plurality of fluid applications, with a high degree ofspecificity and in an economically desirable manner. Having thusdescribed a series of applications and techniques that mayadvantageously exploit monochromatic light of predetermined wavelength,attention is now turned to preferred systems for generating anddelivering monochromatic light to treatment fluids according to thepresent disclosure.

With reference to FIGS. 1 and 2, a treatment apparatus 100 is depictedfor advantageously treating high value/complex fluids according to thepresent disclosure. Treatment apparatus 100 is configured anddimensioned to receive an advantageous light source for generatingsubstantially monochromatic light according to the present disclosure,and is configured to treat high value/complex fluids positioned externalthereto, e.g., blood products, in batch or semi-batch treatmentregimens. Treatment apparatus 100 is merely exemplary of preferredtreatment apparatus according to the present disclosure, as will beapparent from the discussion that follows.

Treatment apparatus 100 includes a housing 102, an inlet port 106adjacent a first end of housing 102, and an outlet port 104 adjacent anopposite end of housing 102. Housing 102 includes an outer wall 103 thatdefines a substantially square cross section. End flanges 107 a, 107 bare provided at either end, each end flange 107 a, 107 b defining asubstantially circular surface 109 that bounds an opening 110. Flanges107 a, 107 b are typically welded to outer wall 103 to define afluid-tight volume 105 (with an inserted light source, as describedbelow) which is in fluid communication with inlet and outlet ports 104,106.

Outer wall 103 and the inner faces of end flanges 107 a, 107 b may beadvantageously fabricated from, or surface treated with, a reflectivematerial, e.g., aluminum. Such reflectivity assists in directingultraviolet radiation toward high value/complex fluids being treated byapparatus 100, as described hereinbelow. Outer wall 103 and end flanges107 a, 107 b may be fabricated from a relatively rigid material havingsufficient strength to withstand the fluid pressure and fluid flowwithin volume 105. Aluminum is a preferred material for use infabricating outer wall 103 and end flanges 107 a, 107 b, although othermetals are also contemplated.

In a preferred embodiment of the present disclosure, housing 102functions as a ground for a light source positioned within volume 105.In such instance, outer wall 103 of housing 102 is necessarilyfabricated from a conductive material, e.g., aluminum, and iselectrically grounded, as is known in the art. The importance of thegrounding properties of housing 102 to advantageous operation ofpreferred systems according to the present disclosure will become morereadily apparent from the light source discussions which follow.

Inlet and outlet ports 106, 104 advantageously communicate with a sourceof cooling fluid (not pictured), preferably a cooling fluid that issubstantially transparent to ultraviolet radiation. For example, inletport 106 may be connected to a source of cooling water thatadvantageously flows through volume 105, and exits housing 102 throughoutlet port 104. Cooling water may be advantageously recycled to housing102 and/or passed through a light source (either before or after passagethrough volume 105), as described in greater detail hereinbelow. Theflow rate of the cooling fluid within volume 105 is controlled throughconventional means, e.g., valving, available water pressure and/or pumpsettings.

A quartz plate 108 is centrally mounted on one face of housing 102 bymounting flange 112 to facilitate passage of light energy from a lightsource (not pictured in FIGS. 1 and 2) positioned within circularpassage 110 to high value/complex fluids positioned external thereto.Quartz plate 108 is advantageously defined by three individual quartzpanels 108 a, 108 b, 108 c to provide a desired level of light energytransmission from housing 102 for treatment of high value/complex fluidspositioned adjacent quartz plate 108. Cross beams 112 a that separatequartz panels 108 a, 108 b, 108 c from one another advantageouslyprovide additional grounding to a light source positioned within housing102, as described below. The external surfaces of quartz panels 108 a,108 b, 108 c define treatment surfaces upon which, or in substantialjuxtaposition with which, high value/complex fluids may be treatedaccording to the present disclosure. By placing the high value/complexfluid in direct contact with quartz plate 108, minimal reflection of themonochromatic light delivered through cooling fluid-containing volume105 and quartz panels 108 a, 108 b, 108 c is permitted.

Of note, high value/complex fluids, e.g., blood products, may bepositioned on the external surfaces of quartz panels 108 a, 108 b, 108 cwithin storage vessel(s) or container(s), e.g., treatment bag(s), thatare highly transparent to ultraviolet radiation, e.g., flexible bagsfabricated from poly(ethylenevinyl acetate), as are known in the art.The storage vessel/container is preferably free of leachable materials.The high value/complex fluids within the storage vessels/containers areadvantageously substantially flattened to define a relatively uniformfluid depth or thickness to be treated according to the presentdisclosure. Mixing of the complex fluid may be provided throughappropriate mechanical means, if desired, during irradiation treatment.Trnasfusion Medicine 7(1) 1 (1993) and Transfusion 30 p 678 (1990).

According to preferred treatment systems according to the presentdisclosure, a non-laser light source is introduced through opening 110in flanges 107 a, 107 b for treatment of high value/complex fluidspositioned adjacent or in juxtaposition with quartz panels 108 a, 108 b,108 c.

With reference to FIG. 3, exemplary non-laser light source 200 isschematically depicted in cross section. Light source 200 issubstantially cylindrical in geometry and is advantageously configuredand dimensioned for introduction into opening 110 of housing 102. Lightsource 200 advantageously rests on circular surfaces 109, therebycentering light source 200 within housing 102 and defining a fluid-tightvolume 105. The ability to introduce and withdraw light source(s) fromhousing 102 is clearly advantageous in numerous respects, including anenhanced ability to service light source(s), as needed, and increasedflexibility in utilizing alternative light source(s) within housing 102,e.g., to generate substantially monochromatic light energy of varyingwavelengths. Alternatively, a light source may be integrally associatedwith housing 102, i.e., non-removable with respect thereto. In suchcase, it is contemplated that the photon-producing gas(es) containedwithin the light source may be replaceable/substitutable. Thus, ineither case, apparatus 100 provides significant versatility in thetreatment of high value/complex fluids with light energy of varyingwavelengths.

Monochromatic light source 200 includes an outer wall 202 and an innerwall 204 that cooperate to define an annulus 206. An elongated conductor208 extends the length of light source 200, preferably along the centralaxis of the light source's cylindrical geometry. A substantiallycylindrical region 210 is defined between inner wall 204 and elongatedconductor 208. Cylindrical region 210 advantageously communicates withinlet and outlet ports for ingress and egress of cooling fluid, e.g.,cooling water. End flanges are provided to define fluid tight seals forannulus 206 and cylindrical region 210. Thus, monochromatic light source200 generally includes three elongated, concentric elements: elongatedconductor 208, cylindrical region 210 and annulus 206.

According to the present disclosure, light emitting, i.e.,photon-producing, gas sources are contained within the bounded volume ofannulus 206. Preferred light emitting/photon-producing gas sources are“excimers,” as are known in the art. Excimer sources (also called“excited dimers”) driven by dielectric barrier discharge offer a unique,advantageous set of capabilities for fluid treatment regimens accordingto the present disclosure: operation at ambient temperature, discretelytunable monochromatic output, variable emitting areas, and highgermicidal UV output per lamp. Dielectric barrier discharge technologyis known for its ability to produce energetic molecular species atambient temperature discharge and is also used to generate ozone.Applicable voltages, frequencies and currents are known to those ofordinary skill in the art. This excitation source allows even high powerexcimer lamps to operate at the same temperature as the fluid to betreated based on the advantageous geometric/structural arrangementsdisclosed herein. As described herein, excimer sources may also be builtin a variety of advantageous geometric configurations. Because the lightgenerating electrical discharge occurs, not as a single large arc, butas a large number of short arcs distributed over a large area, excimersare especially well suited as large area emitters. Similarly, since thelight producing discharge is independent of the size and shape of thelamp, excimers can be used to produce surface emitters of unusual, anduseful, shapes.

Monochromatic light source 200 emits light uniformly over its entiresurface area and is configured to operate at reduced temperatures,particularly based on the system designs disclosed herein. Thesubstantially monochromatic output of light source 200 can be tuned toproduce high spectral irradiance (watts/nm) within peaks of the processaction spectra to maximize the effectiveness of the light energy, e.g.,for pathogen inactivation, leukoreduction, and the like. Excimer sourcesadvantageously produce light output wherein 90% of the output is withina 10 nm band, and preferably a 5 nm bandwidth. The light output may bediscretely adjusted across VUV, UV-A, UV-B and UV-C wavelength regionsby changing the rare and/or halogen gases used. Efficiencies vary withgas mix and geometry from 10% to greater than 30% efficiency, withdemonstrated input powers from less than one watt to greater than 10 kW.

According to the present disclosure, it has been found thatmonochromatic light emission is required to optimally process mostfluids due to the wavelength-specific absorbence characteristics of thefluid, the preservation of critical fluid functions, and/or theefficient delivery of light to produce a desired effect. An irradiationdevice where the emitting surface of the irradiator is both temperaturecontrolled and in contact with the target is highly desirable. In thisway, the unit efficiently delivers light, and controls the temperatureof the sample. This can also be viewed as monochromatic emission sinceheat energy is infrared radiation. For the treatment of fluids with ahigh scattering coefficient system parameters can be optimized tocontrol the sub-surface intensity peak which is produced by backscattered light. This peak is best produced when the light is deliveredto the fluid with a matched refractive index. To do this ideally thereis not an air gap between the lamp and the target fluid—the fluid mustbe in contact with the lamp surface. In the ideal configuration, backscattered photons produce a discreet area of high intensity—essentiallyusing each photon several times to minimize the size and power of therequired light source.

Shorter wavelengths, it is understood, damage the blood component. Lessappreciated is that longer wavelengths can result in repair ofinactivated organisms in a disinfection process, unintended byproductformation when chemical additives are used and, in all cases, heating byinfrared emissions.

Higher intensity sources generally result in faster processing times.However, very intense light sources, like lasers and flash lamps, canalso generate non-linear effects including surface ablation and“two-photon excitation.” Therefore, for all first order processes,defined here as processes that are dependent on dose and/or the numberof absorbed photons, a continuous-duty light source as disclosed hereinprovides optimal dose rates, while minimizing unwanted effects due tohigh intensity. High average power is therefore preferred because itspeeds process times.

According to the present disclosure, excimer light sources may beprovided to deliver a variety of wavelengths based on the gas(es)utilized. Preferred excimer light sources/gas(es) are summarized inTable 1.

TABLE 1 Excimer Gas(es) Wavelength XeI 253 Cl₂ 259 XeBr 282 Br₂ 289 XeCl308 Filtered XeBr 320 I₂ 342 XeF 351

With reference to FIG. 4, light source 200 is typically positionedwithin apparatus 100 by sliding light source 200 through opening 110.Cooling fluid is typically supplied to cylindrical region 210, e.g.,cooling water from a conventional source. Of note, cooling fluid may besupplied in series to apparatus 100 and light source 200. Such coolingfluid may be supplied first to apparatus 100 or to light source 200, andmay flow co-currently or countercurrently within the respectivefluid-tight regions. Treatment fluid 250 is bounded by vessel 252, e.g.,a blood bag or tube and positioned adjacent to or in juxtaposition withquartz panels 108 a, 108 b, 108 c within flange 112, i.e., external tohousing 102. In a preferred embodiment of the present disclosure, thetreatment fluid is a blood product, pharmaceutical, injectable solutionor a vaccine.

Light source 200 is energized to deliver monochromatic light energy bysupplying alternating voltage to elongated conductor 208 andestablishing housing 102 as a ground for the overall system. Voltagesupplied to elongated conductor 208 typically falls within a range of100 to 10,000 volts. The capacitive coupling between the high voltagewithin elongated conductor 208 and grounded housing 102 excites thephoton-producing excimer gas(es) contained within the bounded volume ofannulus 206. Based on the excimer gas(es) contained within annulus 206,substantially monochromatic light of a substantially uniform wavelengthis generated and delivered from annulus 206, i.e., across substantiallythe entire surface area of outer wall 202 and inner wall 204. Themonochromatic light energy is advantageously transmitted through thecooling fluid contained within volume 105 and quartz plate 108 to treatthe treatment fluid 250 within vessel 252 that is positioned adjacent toor in juxtaposition with quartz panel 108. The internal reflectivity ofhousing 102, if any, contributes to maximizing the amount ofmonochromatic light that is transmitted through quartz plate 108 fortreatment of treatment fluid 250. In addition, reflector(s) may be addedto increase flux through quartz plate 108.

In preferred embodiments of the present disclosure, light source 200contains excimer gas(es) selected from those set forth in Table 1hereinabove. Treatment fluid 250 is advantageously selected from amongblood products, pharmaceuticals, injectable solutions and vaccines,although it is further contemplated that other fluids may be treatedaccording to the present disclosure, as described hereinabove. It isfurther contemplated that treatment fluids positioned adjacent to, or injuxtaposition with, quartz plate 108 may contain photoactive compoundsand/or materials, e.g., psoralens and the like, that are activated orotherwise affected by the monochromatic light delivered by light source200.

Preferred treatment parameters vary depending on several factors,including the characteristics of the fluid being treated, the desiredoutcome of the treatment, and the wavelength of the monochromatic lightbeing transmitted by light source 200. However, it is generallycontemplated that fluid treatments according to the present disclosurewill involve delivery of monochromatic light having a wavelength ofbetween 250 and 400 nm; for pathogen inactivation preferably between 260and 310 nm; and for chemical excitation preferably from 220 to 350 nm.The monochromatic light treatment typically involves surface dosages of0.1 to 10 J/cm², based upon intensities of 2 to 50 mW/cm² and treatmenttimes of 5 seconds to 15 minutes.

Several unique advantages are apparent from the fluid treatment regimensdescribed herein. Given the susceptibility of treatment fluids toundesirable heating during treatment, the advantageous continuouscooling of the treatment fluids by cooling fluid within volume 105prevents deleterious effects to the treatment fluids during treatmentwith monochromatic light according to the present disclosure. Beyondcooling, “cooling fluid” that flows through volume 105 may be used tocontrol the temperature of the treatment fluid at any desiredtemperature level, depending on the requirements of the treatmentsystem. Thus, it is contemplated that the “cooling fluid” may be used toheat and/or moderate the temperature of the treatment fluid, as desiredby users of the disclosed system. Moreover, cooling fluid flowing withincylindrical region 210 advantageously facilitates efficient cooling oflight source 200.

Thus, unique aspects of the monochromatic light generation systemaccording to the present disclosure, wherein an excimer light source ispositioned within a fluid-tight, cooling fluid volume, permit reliableand efficacious cooling (or temperature moderation/control) of atreatment fluid through direct heat transfer between the treatment fluidand a substantial heat sink in close proximity thereto. Indeed,according to the present disclosure, it is possible to ensure negligibleheat gains and/or temperature change within a treatment fluid throughoutthe duration of a treatment regimen. The transmission characteristics ofwater permit operation of this design with a wide range of wavelengths.

In addition, monochromatic light energy within the desired UV wavelengthranges that is delivered to treatment fluids according to the presentdisclosure is advantageously generated and transmitted across asubstantial surface area, the geometry of which advantageously conformsor corresponds to the surface area geometry of the treatment fluid.Thus, unlike conventional high intensity bulbs and/or elongatedfluorescent light generation apparatus, which generate light from a“point” or “linear” source, the disclosed treatment systemadvantageously generates monochromatic light through a surface. Theshape of this light emitting surface is directly associated with thefluid-tight enclosure/housing, e.g., mounted thereto. In the disclosedembodiment of FIGS. 1–4, the light emitting surface geometry is definedby quartz panel 108 and is substantially planar. The geometry of thetreatment surface of the treatment fluid 250 substantially conforms orcorresponds to such planar emitting surface, i.e., the treatment surfacegeometry is also substantially planar. The advantageous relationshipbetween the light emitting surface geometry and the fluid treatmentsurface geometry translates into reliable and efficacious energydelivery to the treatment fluid.

Thus, according to the present disclosure, light source(s) for fluid orsurface treatment are advantageously provided wherein the surface areageometry of light source emission conforms/corresponds to the surfacearea geometry of the fluid and/or fluid container to be treated. Surfaceemitter sources that emit uniformly across a large area can be placedclose to the target—providing a very small footprint, high intensities,and a uniform irradiation field. While a planar arrangement as depictedin FIGS. 1–4 provides efficient energy delivery to the treatment fluid,it is contemplated that the fluid container may be a tube, where thelight source is an annulus irradiating inwardly. The container may alsobe a thin sheet, in which case the light source is a plane. Thecontainer may be a bag, in which case the light source may be a hollowvolume, approximating the shape of the bag (similar to a mold) whichradiates inwardly. The container may also be an annulus, in which casethe light source may be a cylinder radiating outwardly, or an annulus(of large diameter) radiating inwardly. In all cases, the surface areaof the light source is engineered to match the fluid container,providing a more uniform dose distribution to the treated volume. Forphotodynamic therapies (PDT), the concept of “vessel” or container forthe treatment fluid can be extended to include the human body or a limbof the body, for whole body irradiation or skin treatment. Hence, lightsources that are surface emitters, as disclosed herein, rather thanpoint sources or linear sources, offer significant treatment advantagesfor high value/complex fluids, as described herein.

While preferred systems according to the present disclosure have beendescribed in some detail with reference to the embodiments of FIGS. 1–4,a range of alternative structural and geometric arrangements fordelivering substantially monochromatic light energy are contemplated.For example, as shown schematically in FIGS. 5 and 6, apparatus 300 maybe utilized to generate and deliver monochromatic light from a lightsource 350. Light source 350 includes an annulus 360 within whichexcimer gas is contained. Alternating voltage is supplied to aconductive screen 370 positioned adjacent an inner wall 365 of annulus360, and a housing (not pictured) that may advantageously surround lightsource 350 typically provides a ground with respect thereto. Housing 350may also function as a reflector to direct light energy inward. Afluid-tight annulus 330 is provided interior of excimer gas-containingannulus 360. A cooling fluid typically flows within fluid-tight annulus,e.g., cooling water or air. Treatment fluid 380 to be treated byapparatus 300 typically flows through central tubular region 390.Tubular region 390 may be an integral component of apparatus 300, or maybe defined by tubing that is introduced to and/or threaded through alongthe central axis of apparatus 300, e.g., as blood is obtained from ortransfused to an individual. Tubing may be advantageously fabricatedfrom Teflon or the like.

A modification of this device uses the treatment fluid as a capacitivemedia to couple power to the gas mixture. This eliminates the need forscreens. (See FIG. 3 as a representative example)

Fluid to be treated by apparatus 300 may be selected from among bloodproducts, pharmaceuticals, injectable solutions, vaccines and otherfluid systems. Cooling fluid within cooling annulus 330 advantageouslyprovides immediate cooling (or temperature control/moderation) oftreatment fluid 380 passing through tubular region 390, thereby ensuringthat undesirable temperature changes do not damage or negatively impactthe treatment fluid 380. Moreover, monochromatic light is generated andinwardly transmitted toward treatment fluid 380 across a substantialsurface area, i.e., the surface area of inner wall 365. The lightemitting surface area geometry across which monochromatic light istransmitted to treatment fluid 380 conforms or corresponds to thetreatment surface geometry for treatment fluid 380 as it passes throughcentral tubular region 390, i.e., an annular surface geometry. Thissystem design (FIGS. 5 and 6) has particular advantages for transfusedblood products where handling of the fluid is to be minimized and tubingis already used to transport fluid from donor to storage to recipient.

With reference to FIG. 7, a cross section side view of a furtheralternative treatment system according to the present disclosure isdepicted. Apparatus 700 includes a symmetric pair of photon-emittingexcimer light sources 702 a, 702 b, each enclosed within a housingdefined by an inner wall 704 and an outer wall 706. The external walls708 of apparatus 700 are grounded at grounds 710 a and 710 b. A screen712 is provided adjacent to, but internal of, inner wall 704. Atreatment fluid 720 is contained within a vessel 722. A fluid-tightregion 724 separates vessel 722 from inner wall 704 of light sources 702a, 702 b. A cooling fluid and/or gas is generally located within region724. The cooling fluid/gas may be statically contained within region 724or may flow therethrough, to provide a desired level of temperaturecontrol/moderation. This design has particular applicability toextracorporeal photophoresis systems, or flow through pathogeninactivation process.

In use, alternating voltage is delivered to screen 712. The voltagegenerated between screen 712 and ground 710 excites the excimer gas(es)contained within light sources 702 a, 702 b. Alternating voltage may beapplied between grounds 710 a and 710 b to excite both light sources 702a, 702 b from a single power supply. Monochromatic light is generatedand delivered through inner wall 704, the cooling fluid/gas containedwithin fluid-tight region 724, and vessel 722 so as to treat fluid 720contained therein. The light emitting surface geometryconforms/corresponds to the treatment geometry, i.e., both aresubstantially planar. Moreover, cooling fluid/gas within region 724provides advantageous temperature control/moderation to treatment fluid720 throughout the treatment regimen. Of note, apparatus 700 may be of arelatively large scale and may operate as light emitting paddles or asradiating walls for an enclosure for use in whole body and/or limbmonochromatic light treatments. An alternate view of the device is shownin FIGS. 11 a and 11 b. As shown in these figures, the fluid to betreated proceeds along the path identified by flow arrow “F”. Gas iscontained within region 920 and power source 930 is electricallyconnected to electrodes 910. An alternating voltage is delivered toelectrodes 910. The specific design points (intensity, total power,area, etc) can be determined for this device for a target flow using thealgorithm also shown in FIG. 10.

With reference to FIG. 8, apparatus 800 is schematically depictedaccording to the present disclosure. Apparatus 800 includes asubstantially elliptical annulus 802 that contains excimer gases formonochromatic light generation and emission. A substantially ellipticalhigh voltage screen 804 is positioned within annulus 802 within afluid-tight region 806. A treatment fluid 808 is positioned centrally toapparatus 800 within a container 810 that defines a substantiallyelliptical outer geometry. Container 810 may be a blood bag or the like.The outer housing of apparatus 800 is grounded (not pictured) to allowexcitation of the excimer gases within annulus 802 upon delivery of highvoltage to screen 804. Fluid-tight region 806 advantageously contains acooling fluid/gas to control/moderate the temperature of treatment fluid808 throughout the treatment thereof. The light emission surface areageometry (substantially elliptical) advantageously conforms to thetreatment surface defined by container 810 (substantially elliptical).

As is readily apparent from the preceding description, an ellipticaldesign is merely exemplary of a non-symmetric geometric designcontemplated according to the present disclosure. However, suchelliptical design is not to be deemed limiting of the scope of thepresent disclosure, and it is to be understood that other non-symmetricgeometric designs are contemplated and offer potential advantages tovarious treatment regimens.

As with most treatment fluids, in treating blood products the lightsource must be configured to operate reliably and economically. Bloodproducts are opaque, i.e., they absorb and scatter light over smalldistances. Blood is also a delicate fluid requiring temperature controland gentle mechanical handling. Blood bags are optimized for the safeand stable storage of blood products, for optimal handling, and tominimize potential contamination, not for efficient irradiation. Basedon inherent limitations associated with blood bags and other bloodcontainers, it would be highly desirable to treat blood products beforethey enter storage bags in the first instance or upon egress therefrom.In other words, it is highly desirable to provide an irradiation devicefor blood products that accommodates real time treatment of flowingblood.

A preferred embodiment for providing real time treatment of flowingblood according to the present disclosure utilizes a light source thatprovides a targeted dose to blood flowing in a tube, e.g., utilizingapparatus 300 of FIGS. 5 and 6, to blood flowing in a sheet or plane,e.g., as shown in FIG. 7, or similar system designs. Several designpoints are used to optimize preferred systems according to the presentdisclosure. First, as with any opaque fluid, light intensity variesgreatly over small distances as light is absorbed (and scattered) by thefluid. Delivery of a uniform dose usually requires thin films. The useof optimized light emitting surfaces will have advantages for treatingcylindrical flows that minimize the dose distribution that complicatestreatment of thin films, including the balancing effects of absorbenceand converging light.

While light intensity drops off with distance as a function ofabsorbence, following Beer's law, dose is dependent on intensity.Therefore, dose is dependent on the thickness of the fluid sample.Over-exposure of some target material may be required to adequately doseanother part of the target. Since turbulence can damage blood products,opportunities to use mixing are generally limited. Thin films havetherefore been used in an effort to deliver a more uniform dose. Thismay not be optimal. For certain fluids at certain wavelengths the lightsystem can be designed to maximize back scattered light. A specificexample is the use of 308 nm light and platelets or plasma where lightpropagation is dominated by scatter. In addition to geometric issues,dose is time dependent. Flow can be optimized to minimize dose range.This is not easily achieved with blood products.

In this regard and with reference to apparatus 300 depicted in FIGS. 5and 6, it is noteworthy that central tubular region 390 may receivetreatment fluid directly, or in an alternative embodiment, centraltubular region 390 may receive a tube or pipe threaded therethrough.Thus, for example, in blood donation and/or blood transfusion systems,tubing passing to or from a patient's body may pass through tubularregion 390, thereby permitting the blood stream to be treated withmonochromatic light from light source 350 in real time, i.e., in theprocess of blood donation and/or in the process of blood transfusion toa recipient. Such blood streams receive immediate and continuous coolingfrom cooling fluid that passes through cooling annulus 330.

Inasmuch as annulus 360 (which contains the excimer gas) surroundstubular region 390 in apparatus 300 of FIGS. 5 and 6, light source 350advantageously simultaneously delivers monochromatic light to atreatment fluid within tubular region 390 from all directions. Thestructural and geometric arrangement thus optimizes light intensitydistribution to the treated fluid, by transmitting light energy inwardlyfrom an annular light transmission surface. The flow of the treatmentfluid through tubular region 390 may also be substantiallynon-turbulent, thereby minimizing the potential damage to treatmentfluids passing therethrough. It is envisioned that a device without ascreen similar to FIG. 11 can be used where the electrical power iscoupled through the treated fluid. The device can be non-cylindrical inconfiguration, as illustrated in FIGS. 7 and 8 or planar as detailed inFIG. 11.

Transfer tubes thus offer an advantageous geometric opportunity becauselight transmission reaches the treatment fluid from multiple directionssimultaneously. A tube irradiated from all sides can have a near optimaluniform dose distribution. Since the proposed light source delivers auniform intensity to the entire surface area of the tube. While light isabsorbed as it travels toward the center of the tube, this effect isopposed by the smaller effective area the light flux must pass through.Total optimization, considering both the absorbance and scatteringcomponents of the fluids optical density, may require only an adjustmentof the tube diameter, as is well within the skill of persons skilled inthe art.

Beyond the inward irradiation systems disclosed in FIGS. 5–8, it isfurther contemplated that the fluid flow may be through an annulussurrounding the excimer gas. In this alternative embodiment,monochromatic light would be radiating both outwardly and inwardlythrough the treatment fluid, with many of the benefits of apparatus 300disclosed hereinabove, e.g., real time treatment, reliable cooling, etc.Of note, in apparatus 300 and other flow designs according to thepresent disclosure, it is contemplated that treated fluid may berecycled (in whole or in part) and/or fed to further treatment apparatusaligned in series for further processing, as may be needed to achievethe desired treatment results. Indeed, it is contemplated that a seriesof treatment apparatus may be arranged in series, with multiple lightsources introducing light energies of differing intensities and/orwavelengths to respective treatment apparatus, thereby expanding thetreatment regimen to target different pathogens and the like.

Thus, treatment apparatus according to the present disclosure are notlimited to the exemplary designs shown in the accompanying figures, butmay take a variety of geometric forms and structural arrangements, aswill be apparent to persons skilled in the art based on the detaileddescription provided herein. Alternative treatment apparatus may thus beutilized, provided the desired monochromatic light irradiates thetreatment fluid for a time and to a degree necessary to achieve thedesired results, without imparting undesirable heating of the treatmentfluid.

To further illustrate advantageous applications of the disclosedtreatment systems, several examples are provided that illustrate certainspecific aspects of the present disclosure. However, it is to beunderstood that these examples are merely exemplary of applications,techniques, systems, methods and apparatus utilizing the disclosedtechnology, and are not to be limitative thereof. Many variations andalternative applications of the disclosed technology that fall withinthe spirit and scope of the present disclosure are contemplated and willbe apparent to those of skill in the art from the detailed descriptionprovided herein, and the examples that follow.

EXAMPLE 1

As depicted in FIGS. 1–4, apparatus 100 was utilized with light source200 positioned therewithin to simulate processing of blood productsusing a photochemically activated process. XeBr was selected as theexcimer gas. The output was filtered using window glass to remove 282 nmlight and pass only the emission centered at 320 nm. Blood productscontained within conventional blood bags were positioned atop quartzplate 108 and irradiated with monochromatic light from the XeBr excimerlight source. Cooling fluid flowing through the treatment apparatusmaintained the blood samples at a constant temperature, and preventedany deleterious effect thereto. Platelets were maintained at 24° C.,based on the cooling fluid being supplied to the system at thattemperature and the platelet bag being in intimate contact with therelatively large surface area of the quartz panels.

Based on irradiations with the XeBr excimer source using the apparatusof FIGS. 1–4, no clinically significant effect on platelets was observedfor exposures greater than 4 J/cm² measured as a change in plateletcount (immediately after irradiation or 24 hours later), CD62,morphology score, LDH, pH, pO2, PCO2 or bicarbonate, osmatoc recovery.Similarly for plasma irradiations>4 J/cm² showed no effect on PT<PTT,fibrogen or Factor VIII. For red cells, measurements includedhematocrit, LDFH, 2,3 D-P-G, % hemolysis and others. No changes wereobserved with surface doses greater than 4 J/cm².

Based on these test results, it was concluded that the disclosedtreatment system was effective in treating blood product samples withoutcausing deleterious effects thereto a shown in tables 2 and 3 and againin FIGS. 12 and 13.

EXAMPLE 2

These experimental studies were designed to show that refractory viralcontaminants can be inactivated using 282 nm light in real bloodproducts using the treatment systems of the present disclosure. Thesystem was evaluated for its ability to inactivate porcine parvovirus(PPV). PPV (NADL-2 strain) is an 18–26 nm, non-enveloped, DNA-containingparvovirus, which exhibits a high degree of resistance to a range ofphysico-chemical reagents. It is not treated using cell washingtechniques because it is non-enveloped. PPV inactivation using psoralenand riboflavin are inefficient because the small genome size of thevirus requires either larger doses of activating compound or longerirradiation times.

The strength (titer) of the production lot of virus used in the studywas determined by a plaque assay utilizing ST indicator cells. GLP labstandards were maintained. The PPV stock solution used in this exampletested positive for identity when tested with a polyclonal antiseraspecific for PPV and is free of potential bovine (BAV, BPI3, BPV, BVDV,IBR, and REO-3) and porcine (PAV and TGE) viral contaminants.

The blood components were not diluted, and were treated as they would bestored in a blood bank. Volumes used (30 to 150 ml) and the size of bagssimulated the thickness of blood product in standard storage bags.Samples which altered the virus titers by>0.5 log₁₀ were considered tointerfere. If the samples showed significant levels of interference, theresults were reviewed prior to proceeding. PPV titers measured as PFU/mLwere reduced by>5 logs for both Fresh Frozen Plasma and Platelets asshown in chart #5.

Fresh Frozen Plasma

Three units of fresh frozen plasma (FFP, approximately 300 mL/unit) werepooled. The pooled mixture was then spiked with 1% of PPV stock solution(exact volumes were recorded at the time of spiking). The spikedstarting materials were then divided into three, 100 mL samples and ten,50 mL samples.

A 6 mL sample of the spiked starting material was removed from one ofthe 100 mL aliquots, adjusted to pH 6.5–7.5 (if necessary) and dividedinto multiple aliquots. One aliquot was tested immediately, theremaining aliquots were snap frozen, and stored as backups at or below−70° C. The remaining 94 mL of sample was held at ambient temperaturefor the duration of the process. Following incubation, a 6 mL sample wasremoved, adjusted to pH 6.5–7.5 (if necessary) and divided into multiplealiquots. One aliquot was tested immediately, the remaining aliquotswere snap frozen, and stored as backups at or below −70° C. Theremaining spiked samples were then treated with 282 nm monochromaticlight in the apparatus of FIGS. 1–4.

Following treatment, a 6 mL aliquot was removed from each treatedsample, adjusted to pH 6.5–7.5 (if necessary) and divided into multiplealiquots. One aliquot was tested immediately, the remaining aliquotswere snap frozen and stored as backups at or below −70° C.

Platelets, RPC

Six units of random platelet concentrates (RPC, approximately 65mL/unit) were pooled. The pooled mixture was then spiked with 1% of PPVstock solution (exact volumes were recorded at the time of spiking). Thespiked material was then divided into three, 60 mL samples and seven, 20mL samples. A 6 mL sample of the spiked starting material was removedfrom one of the 60 mL aliquots, adjusted to pH 6.5–7.5 (if necessary)and divided into multiple aliquots. One aliquot was tested immediately,the remaining aliquots were snap frozen, and stored as backups at orbelow −70° C. The remaining 54 mL of sample was held at ambienttemperature for the duration of the process. Following incubation, a 6mL sample was removed, adjusted to pH 6.5–7.5 (if necessary) and dividedinto multiple aliquots. One aliquot was tested immediately, theremaining aliquots were snap frozen, and stored as backups at or below−70° C. The remaining spiked samples were then treated with 282 nmmonochromatic light in the apparatus of FIGS. 1–4.

Following treatment, a 6 mL aliquot was removed from each treatedsample, adjusted to pH 6.5–7.5 (if necessary) and divided into multiplealiquots. One aliquot was tested immediately, the remaining aliquotswere snap frozen, and stored as backups at or below −70° C.

Results

For both platelets and plasma, the PPV was reduced to non-detectablelevels. The maximum log removal shown is that which could be quantifiedgiven the limits of detection. Extra wells were set for the highest dosemeasurements, and no virus was detected.

Test results are reflected in the following Tables.

TABLE 2 Log₁₀ Reduction Summary - Fresh Frozen Plasma Virus Sample /Volume / Surface Dose / Notes Log₁₀ Reduction PPV FFP / 100 mL / 4 J/cm²/ Mixed 2.24 ± 0.18 FFP / 100 mL / 8 J/cm² / Mixed 3.14 ± 0.16 FFP / 50mL / 1 J/cm² / Mixed 1.27 ± 0.13 FFP / 50 mL / 2 J/cm² / Not mixed 0.97± 0.27 FFP / 50 mL / 2 J/cm² / Mixed 2.03 ± 0.24 FFP / 50 mL / 4 J/cm² /Not mixed 1.02 ± 0.18 FFP / 50 mL / 4 J/cm² / Mixed 2.04 ± 0.25 FFP / 50mL / 8 J/cm² / Not mixed 1.34 ± 0.13 FFP / 50 mL / 8 J/cm² / Mixed 4.24± 0.25 FFP / 50 mL / 16 J/cm² / Not mixed 2.47 ± 0.22 FFP / 50 mL / 16J/cm² / Mixed * > 4.87 ± 0.12    FFP / 50 mL / 32 J/cm² / Mixed * > 4.87± 0.12    * Virus reduced to non-detectable levels.

TABLE 3 Log₁₀ Reduction Summary - Random Platelet Concentrates Log₁₀Virus Sample / Volume / Surface Dose / Notes Reduction PPV RPC/ 60 mL /4 J/cm² / Mixed 2.35 ± 0.21 RPC/ 60 mL / 8 J/cm² / Mixed 4.14 ± 0.21RPC/ 20 mL / 1 J/cm² / Mixed 1.43 ± 0.31 RPC/ 20 mL / 2 J/cm² / Mixed2.42 ± 0.36 RPC/ 20 mL / 4 J/cm² / Mixed 4.90 ± 0.19 RPC/ 20 mL / 8J/cm² / Not mixed 2.95 ± 0.19 RPC/ 20 mL / 8 J/cm² / Mixed * > 5.93 ±0.16    RPC/ 20 mL / 16 J/cm² / Not mixed 4.45 ± 0.19 RPC/ 20 mL / 16J/cm² / Mixed * > 5.93 ± 0.16    * Virus reduced to non-detectablelevels.

Based on the foregoing test results, it is clear that substantiallymonochromatic light at a wavelength of 282 nm delivered in the disclosedtreatment system is effective against porcine parvo virus in both plasmaand platelets.

EXAMPLE 3

In order to establish the effectiveness of longer wavelength lightproduced by the XeBr source, tests were made comparing inactivationrates at 282 nm to those measured at 260 nm. 260 nm is near the peak ofthe germicidal action spectra. Monochromatic light is produced using anexcimer lamp using Cl₂ to produce light at comparable intensities at 260nm. A lab cultured coli was used.

A collimated beam apparatus was used to deliver light to static samplecontainers. Heterotrophic plates counts (HPC) were performed as perStandard Methods Spread Plate Method (9215 C.) (19^(th) Ed). Thisincluded serial diluting the sample by 10 s using 50% Difco nutrientbroth as diluent, pipetting 100 μL of each dilution onto the plates, andspreading the sample with a plastic disposable spreader so that theentire sample is absorbed into the agar media. Samples were incubated(plates inverted) at 32–35° C. and counted for quantification ofheterotrophic bacteria at 24 hours and again at 48 hours and recorded.Only the analytical plate (that with colonies between 30 and 300)

was reported although all counts were recorded in the lab book. Theresulting data, which reflects averages of several runs, is shown in theplot of FIG. 7.

EXAMPLE 4

Example 4 goes farther, showing the removal of PPV at a wavelength of308 nm. See summary FIG. 12, which includes data at 282 nm from tables 2and 3. Removal rates are significantly faster than those at 282 nm. Thissurprising result can be explained by considering both the germicidalefficacy of the light. Considering standard action spectrum for UVdisinfection and the closely related DNA absorption curve, 308 nm lightis less efficient than 260 nm light by a factor of 10–20, and lessefficient than light at 282 nm by a factor of approximately 5. This ismore than counter acted by the substantial change in the absorptioncharacteristics of platelets and plasma between 260 and 300 nm. Theoptical density decreases by a factor of 20—the data in table 3/FIGS. 12a–12 b show that this increase in transmission more than compensates forthe decreased germicidal efficacy. FIG. 13 illustrates that the reducedabsorption by platelets and plasma at 308 nm results in significantlyless damage as well as increased viral inactivation. This surprisingresult is further supported by the appreciation of the importance ofscattering discussed earlier in this disclosure.

Having thus described preferred embodiments and exemplaryuses/applications of the present disclosure, it is to be understood thatthe specifically disclosed forms are merely illustrative of the scope ofthe present disclosure. Various changes may be made in the function andarrangement of parts and processing parameters; equivalent means may besubstituted for those described and/or illustrated; and certain featuresmay be used independently from others without departing from the spiritand scope of the invention as defined in the claims that follow.

1. A non-laser light source assembly adapted to supply light energy whensaid light source is energized comprising a) a housing defined by atleast one outer wall, said at least one outer wall defining an outerface and inner face; b) a light source positioned within said housing;c) means for energizing said light source; d) a bounded volume ofphoton-producing gas positioned within said housing; wherein at least aportion of said outer wall is substantially transparent to photonsproduced by said bounded volume of gas, said substantially transparentportion of said outer wall being temperature-controlled through directcontact of a cooling fluid with the inner face thereof; and wherein saidlight source includes a bounded region that is adapted to receive acooling fluid, and wherein said cooling fluid passes in direct contactwith said inner face of said outer wall and then enters said boundedregion of said light source to provide cooling to said light source. 2.A non-laser light source assembly according to claim 1, wherein saidbounded volume of photon-producing gas generates substantiallymonochromatic light having a wavelength of between 260 nm and 310 nm. 3.A non-laser light source assembly according to claim 1, wherein saidphoton-producing gas is an excimer gas selected from the groupconsisting of XeI, Cl₂, XeBr, Br₂, XeCl, filtered XeBr, I₂ and XeF.
 4. Anon-laser light source assembly according to claim 1, wherein saidsubstantially transparent portion of said outer wall is fabricated fromquartz.
 5. A non-laser light source assembly according to claim 1,wherein said substantially transparent portion of said outer wall istemperature-controlled by a cooling fluid that flows adjacent to theinner face of said outer wall.
 6. A non-laser light source assemblyaccording to claim 1, wherein a treatment fluid is positioned adjacentsaid outer face of said substantially transparent portion of said outerwall, said treatment fluid being selected from the group consisting ofblood products, pharmaceuticals, injectable solutions and vaccines.
 7. Anon-laser light source assembly according to claim 1, further comprisingat least one reflective surface associated with said housing, said atleast one reflective surface being oriented to direct photons producedby said bounded volume of gas toward said substantially transparentportion of said outer wall.
 8. A non-laser light source assemblyaccording to claim 1, wherein said housing functions as a ground forsaid light source.
 9. A non-laser light source assembly according toclaim 1, further comprising at least one flange mounted with respect tosaid outer wall, wherein said substantially transparent portion ismounted to a non-transparent portion of said outer wall by said ateleast one flange.
 10. A non-laser light source assembly according toclaim 9, wherein said substantially transparent portion of said outerwall is defined by a plurality of substantially transparent panels thatare mounted with respect to said non-transparent portion of said outerwall by said at least one flange.
 11. A non-laser light source assemblyaccording to claim 10, wherein said at least one mounting flangeincludes at least one cross beam positioned between adjacentsubstantially transparent panels.
 12. A non-laser light source assemblyaccording to claim 11, wherein said at least one cross beam providegrounding for said light source.
 13. A non-laser light source assemblyaccording to claim 9, wherein said at least one flange defines atreatment region for positioning of a treatment fluid in directjuxtaposition with said substantially transparent portion of said outerwall.
 14. A non-laser light source assembly according to claim 1,wherein said light source is removably positioned within said housing.15. A non-laser light source assembly according to claim 1, wherein abounded region is defined between said at least one outer wall and saidlight source, and wherein said bounded region contains cooling fluid indirect contact with the inner face of said outer wall.
 16. A non-laserlight source assembly according to claim 1, wherein said light sourcegenerates photons that pass through said cooling fluid that is in directcontact with said inner face of said outer wall and through saidsubstantially transparent portion of said outer wall to treat a fluidpositioned in juxtaposition with said outer face of said substantiallytransparent portion of said outer wall.
 17. A non-laser light sourceassembly according to claim 16, wherein said fluid in juxtaposition withsaid outer face is positioned within a container that is substantiallytransparent to ultraviolet radiation.
 18. A non-laser light sourceassembly according to claim 1, further comprising a fluid positionedexternal to said housing and in alignment with said substantiallytransparent portion of said outer wall.
 19. A non-laser light sourceassembly according to claim 18, wherein said fluid positioned externalto said housing and in alignment with said substantially transparentportion of said outer wall is a complex fluid selected from the groupconsisting of a blood product, a pharmaceutical, an injectable solution,and a vaccine.
 20. A non-laser light source assembly according to claim18, wherein said fluid positioned external to said housing and inalignment with said substantially transparent portion of said outer wallis positioned within a container.